Device and method for reducing mitral valve regurgitation

ABSTRACT

In one embodiment, the present invention provides a prosthesis that can be implanted within a heart to at least partially block gaps that may be present between the two mitral valve leaflets. In one preferred embodiment, the prosthesis includes an anchoring ring that expands within the left atrium to anchor the prosthesis and a pocket member fixed to the anchoring ring. When the mitral valve is open, blood flows past the pocket member, maintaining the pocket member in a collapsed state. When the mitral valve closes, the backpressure of the blood pushes into the pocket member, expanding the pocket member to an inflated shape. The mitral valve leaflets contact the expanded pocket member, allowing the prosthesis to block at least a portion of the openings between the leaflets, thereby minimizing regurgitated blood flow into the left atrium.

RELATED APPLICATIONS

The present application is a continuation of U.S. patent applicationSer. No. 12/761,225, filed Apr. 15, 2010, which issued as U.S. Pat. No.8,460,370 on Jun. 11, 2013, which is a continuation of U.S. patentapplication Ser. No. 11/227,642, filed Sep. 14, 2005, which issued asU.S. Pat. No. 7,704,277 on Apr. 27, 2010, which claims priority to U.S.Provisional Application Ser. No. 60/609,345 filed Sep. 14, 2004 and U.S.Provisional Application Ser. No. 60/657,919 filed Mar. 3, 2005; theentire disclosures all of which are hereby incorporated by reference.

BACKGROUND OF THE INVENTION

The mitral valve is one of the most crucial of the four valves of thehuman heart, preventing the regurgitation of blood from the leftventricle into the left atrium during contraction of the heart. Locatedbetween the left atrium and the left ventricle, the mitral valveincludes two leaflets positioned to block blood flow in a closed statewhile allowing blood flow in an opened state.

The mitral valve is opened and closed by a pressure differential betweenthe left atrium and left ventricle and by a complex network ofcollagenous cord-like structures called chordae tendineae that extendfrom the free edges of the mitral valve leaflets to the papillarymuscles on the ventricular wall of the heart. As the papillary musclescontract, they pull on the leaflets and thereby open the mitral valve,allowing blood to flow into the left ventricle. As the papillary musclesrelax, the pull on the leaflets is reduced, causing the mitral valve toclose and thereby block blood flow into the left ventricle.

Normal operation of the mitral valve can be impaired when the valveleaflets fail to coapt or fully close, allowing regurgitated blood toflow back into the left atrium This mitral valve regurgitation is oftencaused by a congenital valve defect or by changes to the heart geometrydue to disease. For example, an infection may cause the mitral valveannulus to enlarge and thereby change the position and orientation ofthe valve leaflets. In another example, a mitral valve defect may causeprolapse or a mismatch of the leaflets, allowing blood flow toregurgitate back into the left atrium.

One early approach to treatment of an insufficient mitral valve involvedsurgical replacement with an artificial valve. In these procedures,open-heart surgery was typically performed on the patient to replace thefaulty valve with either a mechanical or biologically derived valve.While this treatment procedure has been improved with time, significantlimitations still exist. For example, the removal and replacement of amitral valve is highly invasive and therefore greatly increases the riskof serious complications such as infection or rejection.

Other surgical techniques have been developed to reduce the amount ofheart remodeling necessary with valve replacement. One such technique isknown as bowtie repair, in which a center region of each mitral valveleaflet is sutured together. Another technique involves creating aplacation around the valve annulus, thereby reducing the cross-sectionalarea of the valve annulus. While these techniques require lessremodeling than valve replacement, a substantial amount of remodeling isstill required. Further, it can be difficult to evaluate the efficacy ofthe surgical procedure before the conclusion of the surgery.

In yet another technique, an annuloplasty ring is sewn within theannulus of the mitral valve. Since the diameter of the annuloplasty ringis smaller than the diameter of the mitral valve annulus, the leafletsof the valve are moved together, increasing coaptation. In addition toalso being highly invasive, annuloplasty rings generally distort thenatural curved shape of the mitral valve and can further limit thecontractility of the annulus.

While the techniques described above have been used with some successfor the treatment of mitral valve deficiencies, additional treatmentprocedures are needed that require little or no remodeling of the heart.Further, additional treatments are needed that can be performed withminimal invasiveness and yet can more effectively reduce or eliminatemitral valve regurgitation.

OBJECTS AND SUMMARY OF THE INVENTION

It is an object of the present invention to overcome the limitations ofthe prior art.

It is an object of the present invention to provide an improved methodand device for treating mitral valve regurgitation.

It is another object of the present invention to provide a prosthesisdevice that reduces regurgitation of blood into the left atrium.

It is yet another object of the present invention to provide aprosthesis device that can be delivered and deployed percutaneouslywithin a patient.

It is another object of the present invention to provide a prosthesisdevice that can dynamically fill gaps between mitral valve leaflets.

It is another object of the present invention to provide a prosthesisdevice that can reduce most pathologies of mitral valve regurgitation.

The present invention seeks to achieve these objects, as well as othersnot specifically enumerated here, by providing a prosthesis that can beimplanted within a heart to at least partially block gaps that may bepresent between the two mitral valve leaflets. In one preferredembodiment, the prosthesis includes an anchoring ring that expandswithin the left atrium to anchor the prosthesis and a pocket memberfixed to the anchoring ring. The pocket member is positioned within themitral valve, between the leaflets so that an open side of the pocketmember is positioned within the left ventricle. When the mitral valve isopen, blood flows past the pocket member, maintaining the pocket memberin a collapsed state. When the mitral valve closes, the backpressure ofthe blood pushes into the pocket member, expanding the pocket member toan inflated shape. The mitral valve leaflets contact the expanded pocketmember, allowing the prosthesis to block at least a portion of theopenings between the leaflets, thereby minimizing regurgitated bloodflow into the left atrium.

Another preferred embodiment of the present invention provides devicefor treating valve regurgitation comprising:

a coaptation member sized for placement at least partially betweenleaflets of a valve, said coaptation member having an expanded state anda deflated state and having a length substantially equal to a commissureof said leaflets; and

an anchoring structure connected to said coaptation member, saidanchoring structure having a compressed state sized to fit within adelivery catheter and an expanded state sized for fixation on at least aportion of a wall of a chamber adjacent said valve.

Another preferred embodiment of the present invention provides a methodof treating valve regurgitation comprising:

loading a prosthesis within a delivery catheter, said prosthesisincluding an anchoring portion and a coaptation portion;

advancing said delivery catheter to a chamber of a heart;

deploying said coaptation portion within a valve;

expanding said anchoring portion to contact a wall of said chamber; and

supporting said coaptation portion within a commisure of said valve.

Another preferred embodiment of the present invention provides a devicefor substantially blocking blood flow in a valve during systolecomprising:

a flexible member having a lateral dimension;

a support member coupled to said flexible member and shaped to positionsaid lateral dimension of said flexible member along a commissurallength of a leaflet of said valve;

an anchoring member coupled to said support member, said anchoringmember including a compressed configuration and an expandedconfiguration;

wherein said expanded configuration of said anchoring member is shapedto position said support member at least partially within said valve.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A illustrates a front view of a prosthesis according to onepreferred embodiment of the present invention;

FIG. 1B illustrates a perspective view of the prosthesis of FIG. 1A;

FIG. 1C illustrates a profile view of the prosthesis of FIG. 1A in anexpanded configuration;

FIG. 1D illustrates a profile view of the prosthesis of FIG. 1A in andeflated configuration;

FIG. 2A illustrates a bottom view of the prosthesis of FIG. 1A in adeflated configuration within a mitral valve;

FIG. 2B illustrates a bottom view of the prosthesis of FIG. 1A in anexpanded configuration within a mitral valve;

FIG. 3A illustrates a profile view of the prosthesis of FIG. 1A in adeflated configuration within a mitral valve;

FIG. 3B illustrates a profile view of the prosthesis of FIG. 1A in anexpanded configuration within a mitral valve;

FIG. 4 illustrates a front view of the prosthesis of FIG. 1A in adelivery catheter;

FIG. 5A illustrates a front view of a prosthesis according to anotherpreferred embodiment of the present invention;

FIG. 5B illustrates a side view of the prosthesis of FIG. 5A;

FIG. 5C illustrates a perspective view of the prosthesis of FIG. 5A;

FIG. 5D illustrates a perspective view of the prosthesis of FIG. 5A;

FIG. 6 illustrates a side view of the prosthesis of FIG. 5A within aheart;

FIGS. 7A and 7B illustrate a side view of the prosthesis of FIG. 5Awithin a delivery catheter;

FIGS. 8A and 8B illustrate a side view of the prosthesis of FIG. 5A witha retrieval thread;

FIG. 9A illustrates a front view of a prosthesis according to anotherpreferred embodiment of the present invention;

FIG. 9B illustrates a side view of the prosthesis of FIG. 9A;

FIG. 9C illustrates a perspective view of the prosthesis of FIG. 9A;

FIG. 9D illustrates a perspective view of the prosthesis of FIG. 9A;

FIG. 9E illustrates an enlarged view of area 9E in FIG. 9D;

FIG. 10A illustrates a front view of a prosthesis according to anotherpreferred embodiment of the present invention;

FIGS. 10B-10D illustrate various perspective views of the prosthesis ofFIG. 10A;

FIG. 11 illustrates a side view of the prosthesis of FIG. 10A duringdeployment from a delivery catheter;

FIG. 12A illustrates a front view of a prosthesis according to anotherpreferred embodiment of the present invention;

FIG. 12B illustrates a side view of the prosthesis of FIG. 12A;

FIGS. 12C-12E illustrate various perspective views of the prosthesis ofFIG. 12A;

FIG. 13 illustrates a side view of the prosthesis of FIG. 12A within aheart;

FIG. 14A illustrates a front view of a prosthesis according to anotherpreferred embodiment of the present invention;

FIG. 14B illustrates a side view of the prosthesis of FIG. 14A;

FIG. 14C illustrates a top view of the prosthesis of FIG. 14A;

FIGS. 14D and 14E illustrate various perspective views of the prosthesisof FIG. 14A;

FIG. 15 illustrates a side view of the prosthesis of FIG. 14A within aheart;

FIGS. 16A and 16B illustrate side views of the prosthesis of FIG. 14Awithin a delivery catheter;

FIG. 17A illustrates a front view of a prosthesis according to anotherpreferred embodiment of the present invention;

FIG. 17B illustrates a top view of the prosthesis of FIG. 17A;

FIGS. 17C and 17D illustrate perspective views of the prosthesis of FIG.17A;

FIG. 18A illustrates a front view of a prosthesis according to anotherpreferred embodiment of the present invention;

FIGS. 18B and 18C illustrate various perspective views of the prosthesisof FIG. 18A;

FIG. 18D illustrates an enlarged view or area 18D in FIGS. 18B;

FIG. 19A illustrates a front view of a prosthesis according to anotherpreferred embodiment of the present invention;

FIGS. 19B and 19C illustrate various perspective views of the prosthesisof FIG. 19A;

FIG. 19D illustrates an enlarged view or area 19D in FIG. 19B;

FIG. 20A illustrates a front view of a prosthesis according to anotherpreferred embodiment of the present invention;

FIGS. 20B and 20C illustrate various perspective views of the prosthesisof FIG. 20A;

FIG. 21A illustrates a side view of the prosthesis of FIG. 20A in apartially deployed configuration;

FIG. 21B illustrates an enlarged view of area 21B in FIG. 21A;

FIG. 22A illustrates a front view of a prosthesis according to anotherpreferred embodiment of the present invention;

FIGS. 22B and 22C illustrate various perspective views of the prosthesisof FIG. 22A;

FIG. 23A illustrates a front view of a prosthesis according to anotherpreferred embodiment of the present invention;

FIG. 23B illustrates a top view of the prosthesis of FIG. 23A;

FIGS. 23C and 23D illustrate various perspective views of the prosthesisof FIG. 20A;

FIG. 24A illustrates a front view of a prosthesis according to anotherpreferred embodiment of the present invention;

FIG. 24B illustrates a side view of the prosthesis of FIG. 23A;

FIGS. 24C and 24D illustrate various perspective views of the prosthesisof FIG. 20A;

FIG. 24E illustrates an enlarged view of area 24E in FIG. 24D;

FIG. 25 illustrates a side view of a prosthesis within a heart accordingto another preferred embodiment of the present invention;

FIG. 26A illustrates a side view of a prosthesis within a heartaccording to another preferred embodiment of the present invention; and

FIG. 26B illustrates a cross-sectional view of the prosthesis of FIG.26A.

DETAILED DESCRIPTION OF THE INVENTION

The present invention seeks to reduce the amount of blood that flowsinto the left atrium from the left ventricle during the systole phase ofheart contraction. Most instances of this mitral valve regurgitation arecaused by poor coaptation of the mitral valve leaflets that createopenings between these leaflets when the mitral valve is closed. Thepresent invention decreases the size of these opening between the mitralvalve leaflets, and in some cases completely eliminates the openings,allowing the mitral valve to function with little or no regurgitation.This is achieved in at least some of the example embodiments describedin this specification by positioning a member between the two mitralvalve leaflets to close or fill up the openings between the leafletswhen closed.

FIGS. 1A-4

One such design can be seen in FIGS. 1A-4 which illustrates a preferredembodiment of a prosthesis 100 according to the present invention. Theprosthesis 100 includes a pocket 106 formed from flexible material 104disposed on a ring 102. As best seen in FIG. 1B, the pocket 106 includesa lower open end 106A that, when properly oriented within a mitral valve120 of a heart 124, expands as the mitral valve 120 closes, blocking anyopenings between the mitral valve leaflets 122. Further, the pocket 106contracts or deflates as the mitral valve 120 opens, maximizing bloodflow from a left atrium 126 to a left ventricle 128. In this sense, thepocket 106 can more generally be described as an expandable occludingmember or a coaptation member.

The pocket 106 is preferably created by gluing, stitching, or otherwiseadhering at least two layers of the flexible material 104 at or aroundline 108. These layers can be achieved with two distinct pieces ofmaterial, or a single piece of material folded against itself.Preferably, the flexible material 104 is made from pericardial tissue orother biological or artificial materials with similar flexibilities,such as bovine tissue, polyurethane, or as described in U.S. Pat. No.6,764,510, the contents of which are herein incorporated by reference.The shape of the pocket 106 and the flexibility of the flexible fabric108 allow the pocket 106 to achieve a deflated position, as best seen inFIGS. 1D, 2A and 3A and an expanded position as best seen in FIGS. 1C,2B and 3B.

While the pocket 106 can be shaped in a variety of differentconfigurations, pocket shapes that facilitate entry and escape of bloodfrom the pocket 106, such as the rounded arch-shape of pocket 106, arepreferred. Configurations of the pocket 106 that include sharp cornersor rough seams are less preferred due to their disruptive effect onblood flow into and out of the pocket 106. Preferably, the pocket 106also includes an overall length similar to that of the mitral valve 120and more preferably substantially the length of the mitral valvecommissure, allowing the pocket 106 to fill any openings that may bepresent along the length of leaflets 122, as seen best in FIG. 2B. Whilea single pocket 106 is preferred, additional pockets or partitionswithin the pocket can also be included in the present invention.

The ring 102 is preferably made from an elastic, shape-memory materialsuch as Nitinol which allows the prosthesis 100 to be compressed orloaded into a delivery catheter 110, as seen in FIG. 4, then expanded toa predetermined shape within the left atrium 126, as seen in FIGS. 3Aand 3B. The ring 102 is sized to press against the walls of the leftatrium 126 of the heart 124, and in some configurations within thecommissure of the mitral valve 120, thereby anchoring the position ofthe prosthesis 100, while positioning the pocket 106 at least partiallythrough a mitral valve 120. Additionally, the lower open end 106A of thepocket 106 is positioned near or within the left ventricle 128. In thissense, the ring 102 can more generally be described as an anchoringframework or an anchoring structure.

Once positioned within the heart 124, the prosthesis 100 functions in asimilar manner to a heart valve, opening during diastole and closingduring systole. More specifically, as blood enters the left atrium fromthe pulmonary veins 125 near the top of the left atrium 126, the bloodflow moves downward towards the mitral valve 120. As the blood flowreaches the mitral valve 120, it pushes against the mitral valveleaflets 122 as the mitral valve 120 is opened by the papillary muscles.The blood flow also pushes against the pocket 106 of the prosthesis 100,forcing out any blood that may be within the pocket 106 and causing thepocket 106 to assume a substantially deflated or compressed position, asseen in FIG. 3A. This compressed configuration of the pocket 106provides a streamline profile that minimizes blood flow resistance andother disruptive effects that a device within the left atrium mightotherwise cause. In this respect, the blood flow during diastole passesinto the left atrium 126, through the mitral valve 120 and past theprosthesis 100 to allow passage of the blood flow into the leftventricle 128.

During systole, backpressure from the blood in the left ventricle 128presses against the mitral valve leaflets 122, as the papillary musclesmove these leaflets 122 to a closed position. Additionally, thisbackpressure of blood in the left ventricle 128 enters the pocket 106 ofthe prosthesis 100, causing the pocket 106 to achieve an expanded shape,as seen in FIG. 3B. The mitral valve leaflets 124 coapt against theexpanded pocket 106, as best seen in FIG. 2B, minimizing or eveneliminating gaps that would otherwise be present between the twoleaflets 122. Thus, blood flow during systole expands the prosthesis 100to reduce or eliminate any openings that would otherwise be presentbetween the leaflets 122, ultimately reducing or preventingregurgitation of blood into the left atrium 126.

Due in part to the dynamic, flexible nature of the pocket 106, theprosthesis 100 can expand to fill a wide range of opening sizes betweenthe leaflets 122 without the need for an equally wide range of pocketsizes. In other words, the same size pocket 106 can expand to fill arelatively small opening or a relatively large opening between themitral valve leaflets 122. Thus, the same size prosthesis 100 may beappropriate for a patient with relatively severe mitral valveregurgitation as well as relatively mild mitral valve regurgitation.Different sizes of prosthesis 100 may be appropriate, however, fordifferent size mitral valves 120, since it is preferred that the pocket106 extends along the length of the commissure of the mitral valve orthe length of the “meeting line” between the two leaflets.

The prosthesis 100 is preferably delivered to the left atrium 126percutaneously by a catheter 110, as seen in FIG. 4. For example, thedelivery catheter 110 may be fed through the femoral vein, into theright atrium and passed through a pre-made puncture in the atrial septum125. In another example, the delivery catheter 110 can be passed throughthe femoral artery into the aorta, through the aortic valve and into theleft ventricle.

Alternately, the prosthesis 100 can be inserted into the left atrium 126through an opening in the atrial wall of the heart 125 during open-heartsurgery. Although the prosthesis 100 can be seen and positioned moreeasily during open-heart procedures, percutaneous delivery is lessinvasive and therefore includes a substantially lower risk ofcomplications.

FIGS. 5A-8B

Another preferred embodiment of a prosthesis 200 according to thepresent invention can be seen in FIGS. 5A-7B. While generally similar tothe prosthesis 100, the prosthesis 200 also includes four anchoringloops 202 that expand to anchor the prosthesis 200 within the leftatrium 126 and position a pocket 206 between the mitral valve leaflets122, along the length of the mitral valve commissure. In this respect,the anchoring loops 202 can more generally be described as an anchoringframework or an anchoring structure.

The pocket 206 is supported by support arms 204 and bottom support 208which provide a support framework for the pocket 206. Preferably theside arms 204 and the bottom support 208 are a single, unitary wire thatconnect to the anchoring loops 202, however multiple segments of wirecan be connected together, for example by welding or soldering, as well.As with the previously described embodiment of the prosthesis 100, thesupport arms 204 and the bottom support 208 are preferably composed ofan elastic, memory-shape material, such as Nitinol, which allows theprosthesis 200 to be compressed and loaded into a catheter 110, as seenin FIGS. 7A and 7B, then deployed to the predetermined shape seen inFIGS. 5A-6. Preferably, the wires used for the support arms 204 and thebottom support 208 are sized and shaped to cause minimal deformation ofthe free edges of the leaflets 122, and therefore minimize distortion ofthe mitral valve geometry. In this respect, the pocket support arms 204can alternatively be described as a framework, a support structure, or apositioning frame.

The pocket 206 is similar to the pocket 106 of the previous embodiment,preferably being composed of a flexible biological or artificialmaterial that is sized and shaped to form a pocket-shape with an openingdirected opposite to the anchoring loops 202. The pocket 206 can bedirectly stitched, glued, or adhered to the outer support arms 204 forsupport. Alternately, the flexible fabric of the pocket 206 can bestitched to form an elongated passage for the support arms 204 on theouter surface of the pocket 206.

As best seen in FIG. 6, the pocket 206 is positioned at least partiallywithin the mitral valve 120 so that the open end of the pocket 206 isfaced toward the left ventricle 128. In this configuration, the pocket206 is deflated during diastole, minimizing blood flow blockage in themitral valve 120, and expanded during systole, at least partiallyfilling any openings between the mitral valve leaflets 122 and therebyminimizing blood flow regurgitation into the left atrium 126.

The prosthesis 200 is preferably delivered to the left atrium 126 by apercutaneous delivery catheter 110 but can also be implanted duringopen-heart surgery, as described in regards to the prosthesis 100. Sincethe pocket 206 has a horizontally elongated shape that requires aspecific orientation within the mitral valve 120, percutaneous deliveryof the prosthesis 200 to the proper position may be more difficult thandelivery during open-heart surgery. Accordingly, the delivery catheter110 may include a retrieval thread 210 and a push rod 212 as seen inFIGS. 8A and 8 b to retrieve the prosthesis 200 back into the catheter110 and redeploy the prosthesis 200 at a new position within the leftatrium 126.

Preferably, the retrieval thread 210 is composed of a thin but strongmaterial such as metal, silk, or polypropylene, and is a single segment.Both free ends of the retrieval thread 210 are positioned at a proximalend of the delivery catheter 110, while the body of the thread 210extends through the deliver catheter 110, through each anchoring loop202 and back through the catheter 110.

Depending on the configuration of the prosthesis 200 in an expandedstate, the retrieval thread 210 alone may not provide the necessaryforce to fully recompress and recapture the prosthesis 200. In suchsituations, the pusher rod 212 may be used in conjunction with theretrieval thread 210 to manipulate the prosthesis 200 into a shapeacceptable for recapture within the delivery catheter 110. For example,the operator of the delivery catheter 110 may pull on the retrievalthread 210 while pushing on the anchoring loops 202 with the pusher rod212. The simultaneous pushing and pulling deform the anchoring loops 202into an elongated shape that can more easily be recaptured by thedelivery catheter 110, allow the user to reposition the distal end ofthe delivery catheter 110 and redeploy the prosthesis 200.

FIGS. 9A-9E

FIGS. 9A-9E illustrate another preferred embodiment of a prosthesis 250that is mostly similar to the prosthesis 200 previously shown in FIGS.5A-8B, having anchoring loops 252 fixed to support arms 258 and a pocket254 disposed between the support arms 256. However, as best seen in FIG.9E, the support arms 258 of the present prosthesis 250 are positionedand attached within the pocket 254 instead of on the outer surface ofthe pocket 254, creating a more uniform outer surface shape comparedwith the prosthesis 200. Additionally, the bottom support 256 includes aloop 256A that is configured to exert force against the support arms 258to maintain the pocket 254 in a fully expanded position.

FIGS. 10A-11

FIGS. 10A-11 illustrate yet another embodiment of a prosthesis 300according to the present invention that is generally similar to thepreviously described embodiments of this specification, having supportarms 304 that support a pocket 306 made from flexible material.

Unlike the embodiments previously described in this specification, theprosthesis 300 includes an anchoring cage 302 that is unitary with thesupport arms 304. Preferably, both the anchoring cage 302 and thesupport arms 304 are cut from a single metal tube, such as by lasercutting the desired pattern into the tube or by other techniques used tomanufacture stents. The metal of the tube is preferably composed a shapememory material, such as those commonly used for stents such as Nitinol.In this regard, the anchoring cage 302 can more generally be describedas an anchoring framework or an anchoring structure.

Once expanded within the left atrium 126, the anchoring cage 302contacts the tissue of the left atrium 126 in more positions thatembodiments previously described in this specification and thereforemore uniformly distributes the anchoring force within the left atrium126. Additionally, the expanded shape of the anchoring cage 302 can beshaped to better conform to the geometry of the left atrium 126 andtherefore more precisely position the pocket 306 at a desired location.

As with the previously described embodiments of this specification, theprosthesis 300 is preferably delivered percutaneously with a deliverycatheter 110 as seen in FIG. 11, but may alternately be deployed duringopen-heart surgery. In the case of percutaneous deployment, theprosthesis 300 compresses to a relatively small pre-deployed state, asseen in FIG. 11.

FIGS. 12A-13

FIGS. 12A-13 illustrate another preferred embodiment of a prosthesis 400according to the present invention, which is generally similar to thepreviously described embodiments, such as the prosthesis 200 shown inFIGS. 5A-8B. More specifically, the similarities of the prosthesis 400include anchoring loops 402 that anchor and position a pocket 406 viasupport arms 404. The pocket 406 is similarly positioned within themitral valve 120 so as to expand into any openings between the mitralvalve leaflets 122 when the mitral valve 120 is closed.

In contrast to the previously described embodiments, the prosthesis 400includes multiple anchoring loops 402 that form a spherical, lemon shapehaving a terminating region 408. The overall shape of the anchoringloops 402 expand to apply pressure against the left atrium 126 atdifferent angles which better maintains the position of the prosthesis400. Additionally, the terminating region 408 can press against thetissue of the left atrium 126 or can alternatively be positioned withinan incision within the wall of the left atrium 126 (e.g. a percutaneousaccess incision within the atrium septum) to provide further anchoringsupport.

The body of the prosthesis 400 includes wires 402A-402E that are shapedto form the anchoring loops 402, as well as two pocket supports 404.Wires 402B, 402C, and 402D are shaped to have a generally circular shapewith each of the free ends captured by terminating region 408. In thisrespect, each wire 402B, 402C, and 402D forms a single loop of theprosthesis 400.

One end of wire 402A is fixed within terminating region 408 while theother end extends down to form a pocket support 404, including anarch-shape in between the two ends having a similar shape to thoseformed by wires 402B, 402C, and 402D. The second pocket support 404 isformed from wire 404E which is similarly fixed within terminating region408. As with the previously described embodiments described in thisspecification, the pocket 406 is fixed to the pocket supports 404,thereby maintaining the pocket 406 at a desired location within themitral valve 120, as best seen in FIG. 13. In this regard, the anchoringloops 402 can more generally be described as an anchoring framework oran anchoring structure.

FIGS. 14A-16B

In another preferred embodiment illustrated in FIGS. 14A-16B, aprosthesis 500 is shown according to the present invention. Similar toprevious embodiments discussed within this specification, the prosthesis500 includes a pocket 506 that is supported and positioned by ananchoring wire 502. While the present prosthesis 500 includes curvedanchoring regions 502A, similar to the curved anchoring wires ofpreviously discussed embodiments, these anchoring regions 502A arecomposed of a single anchoring wire 502. By using a single anchoringwire 502, the prosthesis 500 minimizes the possible sharp ends or edgesthat may otherwise be present. In this sense, the anchoring wire 502 canmore generally be described as an anchoring framework or an anchoringstructure.

As seen in FIGS. 16A and 16B, one possible delivery method of theprosthesis 500 includes compressing or loading the prosthesis 500 withinthe percutaneous delivery catheter 110 and delivering the prosthesis 500to the left atrium 126. Once within the left atrium 126, the prosthesis500 expands to the predefined shape seen in FIG. 15. Thus, theprosthesis 500 maintains the position of the pocket 506 within themitral valve 120, similar to previously discussed embodiments, reducingregurgitation.

FIGS. 17A-17D

FIGS. 17A-17D illustrate yet another preferred embodiment of aprosthesis 600 according to the present invention that reduces mitralvalve regurgitation similar to the embodiments previously described inthis specification by anchoring a pocket 606 within the mitral valve120.

In contrast, present prosthesis 600 includes anchoring wires 602 shapedto have an asymmetrical egg structure that more closely resembles theasymmetrical interior of the left atrium 126. Since the asymmetry of theanchoring wires 602 matches the natural asymmetry of the left atrium126, the prosthesis 600 expands and orients itself in a predeterminedposition, providing stable anchoring and consistent alignment of thepocket 606 with the mitral valve 120. Further, this asymmetrical designfacilitates delivery and deployment from the position of an incisionthrough the atrial septum, since the prosthesis 600 expands to firmlyengage the geometry of the left atrium 126. In this regard, theanchoring wires 602 can more generally be described as an anchoringframework or an anchoring structure.

The pocket 606 also includes a radial or cylinder shape when fullyexpanded, and can more generally be described as an expandable occludingmember or a coaptation member. The radial shape imparts a uniformhydraulic function that is similar, regardless of the rotationallyorientation of the pocket 606 relative to the mitral valve leaflets 122(i.e. the commissure of the mitral valve 120). In this respect, theprosthesis 600 can be deployed to a greater number of orientationswithout adversely affecting the reduction of regurgitation.

FIGS. 18A-18D

FIGS. 18A-18D show another preferred embodiment of a prosthesis 700according to the present invention that is much like the previouslydescribed prosthesis 600, having anchoring wires 702 forming anasymmetrical shape similar to the geometry of the left atrium 126.However, the present prosthesis 700 includes a pocket 706 with anelongated, non-radial shape that is coupled to the anchoring wires 702by a rotating swivel 710. The swivel 710 allows rotation between thepocket 706 and the anchoring wires 702, allowing the pocket 706 toachieve a desired rotational orientation within the mitral valve 120,regardless of the orientation of the anchoring wires 702. In thisrespect, the anchoring wires 702 can more generally be described as ananchoring framework or an anchoring structure.

As best seen in FIG. 18D, the swivel 710 is composed of wire loop 708that extends from an unseen wire support of the pocket 706. Theanchoring wires 702 include a wire coil 704 that encircles and therebyengages the wire loop 708, allowing the anchoring wires 702 to rotate inrelation to the pocket 706. In this respect, the surgeon can more easilydeploy the prosthesis 700 percutaneously by first positioning the pocket706 at a desired position within the mitral valve 120, then deployingthe anchoring wires 702 without the need to adjust the overallrotational orientation of the prosthesis 700. Additionally, the abilityof the prosthesis 700 to rotate allows the pocket 706 to self align sothat each mitral valve leaflet 122 contacts against an elongated side ofthe pocket 706.

FIGS. 19A-19D

FIGS. 19A-19D illustrate a preferred embodiment of a prosthesis 800 thatis similar to the embodiments previously described in thisspecification, especially the prosthesis 700 shown in FIGS. 18A-18D.More specifically, the prosthesis 800 includes anchoring wires 802 whichexpand to an asymmetrical shape, similar to the geometry of the leftatrium 126. Additionally, the prosthesis 800 includes an elongatedpocket 806 coupled to the anchoring wires 802 by a rotating joint 810.In this regard, the anchoring wires 802 can more generally be describedas an anchoring framework or an anchoring structure.

In contrast to the previously described prosthesis 700, the prosthesis800 includes a pocket support wire 804 that not only supports thestructure of the pocket 806, as described in other embodiments in thisspecification, but also wraps around a cylinder 808, then branchesradially outward into loop shapes 804A, as best seen in FIG. 19D. Theends of anchoring wires 802 are coupled within the cylinder 808 so as toallow the anchoring wires 806 rotate freely from the pocket 806.

The looped regions 804A of the pocket support wire 804 assist the freelyrotating pocket 806 in orienting itself to a desired position within themitral valve 120. Additionally, these outer looped regions 804A can besized and shaped to provide support to the pocket 806 by resting on theannulus of the mitral valve 120.

Alternately, the looped regions of the pocket support wire 804 can beshaped to at least partially interlock with a portion of the anchoringwires 802 to allow the anchoring wires 802 to freely rotate within arange, determined and therefore restricted by the length of the loops ofthe pocket support wire 804. Such a rotational restriction may betterassist the surgeon in delivering and deploying by allowing at least somedegree of rotational control over the pocket 806 in a deployedconfiguration.

FIGS. 20A-21B

FIGS. 20A-21B illustrate yet another preferred embodiment of aprosthesis 900 according to the present invention which is generallysimilar to the previously discussed embodiments of this specification,such as prosthesis 600 of FIGS. 17A-17D. For example, the prosthesis 900includes a pocket 906 having a radial shape and pocket support wires908, as well as anchoring wires 902 fixed to the pocket 906 and havingan asymmetrical shape generally matching the inner geometry of the leftatrium 126.

However, the prosthesis 900 includes two separately deployable supportstructures: the previously mentioned anchoring wires 902 and innersupport wires 904. The inner support wires 904 include elongated region904A and anchoring region 904B which continues within the pocket 906 assupport wires 908. The anchoring wires 902 and inner support wires 904can more generally be described as an an anchoring framework or ananchoring structure.

As best seen in FIGS. 21A and 21B, the support structures 902 and 904can be deployed separately during a percutaneous deliver with thedeliver catheter 110. As the prosthesis 900 is pushed out of thedelivery catheter 110, the inner support wire 904, including elongatedregion 904A and anchoring region 904B, expand first while the anchoringwires 902 remain relatively compressed.

The expanded shape of the anchoring region 904B is preferably sized andshaped to engage at least a portion of the annulus of the mitral valve120. In this respect, the user can direct the pocket 906 to a desiredposition within the mitral valve 120 while the anchoring region 904Bexpands to at least partially anchor the pocket 906 in place. Once theuser has achieved a desired position for the pocket 906, the remaininganchoring wires 902 can be deployed from the delivery catheter 110,allowing them to expand to press against the left ventricle 126, therebyfurther anchoring the prosthesis 900 in place.

FIGS. 22A-22C

FIGS. 22A-22C illustrate yet another preferred embodiment of aprosthesis 1000 according to the present invention. Generally, thisprosthesis 1000 is similar to the embodiments previously described inthis specification, such as prosthesis 600 of FIGS. 17A-17D, includinganchoring wires 1002, pocket support wires 1004, and pocket 10006 havinga radial shape.

In addition to these similarities, the prosthesis 1000 includes region1002A of anchoring wires 1002 that curve towards the open end of thepocket 1006. When expanded within the left atrium 126, the region 1002Aof the present invention at least partially contacts the annulus of themitral valve 120. This annulus support prevents the pocket 1006 frombeing pushed past the mitral valve 120 into the left ventricle 128,maintaining the overall vertical position of the prosthesis within theleft atrium 120. In this respect, the anchoring wires 1002 can moregenerally be described as an anchoring framework or an anchoringstructure.

FIGS. 23A-23D

Turning now to FIGS. 23A-23D, yet another preferred embodiment of aprosthesis 1100 according to the present invention is shown. Again, thisprosthesis is generally similar to the previous embodiments described inthis specification, including a pocket 1106 having an elongated shape,anchoring wires 1102, and lower loops 1104 that partially support thepocket 1106 and extent out from a top portion of the pocket 1106.

However, the free ends of the anchoring wires 1102 are wound aroundlower loops 1104, allowing the loops of anchoring wire 1102 to pivot onthe lower loops 1104 to achieve more complex anchoring configurations.By achieve more complex anchoring configurations, the prosthesis 1100can provide better support and therefore more constant positioning ofthe pocket 1106 over time. In this regard, the anchoring wires 1102 canmore generally be described as an anchoring framework or an anchoringstructure.

FIGS. 24A-24E

FIGS. 24A-24E illustrate another preferred embodiment of a prosthesis1200 according to the present invention, having a pocket 1206 with anelongated shape, a pivot loop 1204 that is part of an unseen pocketsupport wire within the pocket 1206, and an anchoring wire 1202 having aregion 1210 wound around the pivot loop 1204 to form a freely rotatingpivot 1212.

To achieve additional complexity with the design of the anchoring wire1202, portions of the anchoring wire fixed to each other with knitting1208, as best seen in FIG. 24E. By achieving additional complexity andlooping structures, the prosthesis 1200 may be better able to anchor andtherefore secure itself within the left atrium 126. Further, theknitting 1208 allows the bound regions of the anchoring wire 1202 tohinge relative to each other, which can allow more efficient packingwithin a delivery catheter 110 or more complex deployment strategieswithin the left ventricle 126. In this respect, the anchoring wire 1202can more generally be described as an anchoring framework or ananchoring structure.

FIG. 25

Turning to FIG. 25, yet another preferred embodiment of a prosthesis1300 is illustrated according to the present invention. Specifically,prosthesis 1300 demonstrates a pocket 1306 having pocket supports 1304,generally similar to the embodiments previously described in thisspecification, and further including a stent anchor 1302 coupled to thepocket supports 1304. In this respect, the stent anchor 1302 can moregenerally be described as an anchoring framework or an anchoringstructure.

The stent anchor 1302 can be composed of a variety of differentmaterials and structures as is known in the art. For example, some stenttechniques can be seen in U.S. Pat. Nos. 6,936,067; 6,929,658;6,926,743; 6,923,828; and 6,902,575; the contents of each are hereinincorporated by reference.

FIGS. 26A-26B

Turning to FIGS. 26A and 26B, yet another preferred embodiment of aprosthesis 1400 is illustrated according to the present invention, whichincludes an alternative anchoring and positioning system for a pocket1406. Specifically, a positioning arm 1402 anchors within the atrialseptum 125, having multiple septum attachment arms 1402 that extend fromthe base of the positioning arm 1402 and press against both the rightand left sides of the atrial septum 125. Preferably, the septumattachment arms 1402 are similar in size and shape to those in atrialseptal closure devices known in the art. To this end, the positioningarm 1402 can more generally be described as an anchoring framework or ananchoring structure.

In this respect, the prosthesis 1400 can be delivered via an incision inthe atrial septum 125, first positioning the pocket 1406 within themitral valve 120, then extending the septum attachment arms 1404 againstboth the left and right sides of the atrial septum 125 for anchoringsupport. The positioning arm 1402 substantially occludes the incisionwithin the atrial septum 125, while the septum attachment arms 1402retain the septal tissue around the positioning arm 1402, preventingblood from passing between through the septum 125.

While the preferred embodiments disclosed in this specification includeexpandable pockets, it should be understood that other designs can beused with the anchoring designs contemplated by the present invention.For example, a solid and preferably flexible plate member canalternatively be used, having a similar shape and size as described inregards to the pockets of the embodiments of this specification.

Preferably, the solid member is relatively soft, having a flexibilitythat allows some compression, especially when contacted by mitral valveleaflets. More preferably, the solid member could be created by adheringtwo pieces of pericardial tissue together and providing supportingmembers or wires similar to those described in regards to the pocket inthe previous embodiments. In place of supporting members, Nitinol stringmay be attached to both the solid member and the left ventricle 128,preventing the solid member from moving into the left atrium 126.Alternatively, the solid member can be composed of a resilient,biocompatible polymer material such as polyurethane.

Preferably, the embodiments of this specification may also includeflexible polymeric sheets, such as polyurethane, that connect theanchoring loops or anchoring wire that contact the left atrium 126. Inthis respect, the flexible sheets further decreases stress on the leftatrium walls by more evenly distributing anchoring force.

It should be understood different elements of the embodiments of thisapplication can be combine to form additional design contemplated by thepresent invention. For example, the septal anchoring prosthesis 1400shown in FIGS. 26A and 26B may be combine with the anchoring structuresshown with the prosthesis 900 of FIGS. 20A-20C.

While the embodiments disclosed in the present invention have beenspecifically described as used with the mitral valve of the heart, it isalso contemplated that these embodiments may be adapted for use withother heart valves. For example, the anchoring structures can bemodified to press against a different geometry within the heart and thepocket can be adapted to a different shaped valve, such as a tricuspidvalve.

Although the invention has been described in terms of particularembodiments and applications, one of ordinary skill in the art, in lightof this teaching, can generate additional embodiments and modificationswithout departing from the spirit of or exceeding the scope of theclaimed invention. Accordingly, it is to be understood that the drawingsand descriptions herein are proffered by way of example to facilitatecomprehension of the invention and should not be construed to limit thescope thereof.

What is claimed is:
 1. A device for treating mitral valve regurgitationcomprising: a coaptation member having an elongated cross-sectionalprofile, the cross-sectional profile having a width in a first radialdirection and a length in a second radial direction, the widthsubstantially smaller than the length, the elongated profile sized forplacement at least partially between leaflets of a native mitral valve,the coaptation member convertible between an expanded configuration anda contracted configuration in response to changes in pressure, the widthin the expanded configuration greater than the width in the contractedconfiguration, while the length is substantially constant in theexpanded configuration and the contracted configuration, the coaptationmember in the expanded configuration restricting blood flow between theleaflets and the coaptation member, and the coaptation member in thecontracted configuration allowing blood to flow between the leaflets andthe coaptation member; a support structure coupled to the coaptationmember, the support structure providing the coaptation member with theelongated cross-sectional profile, wherein the support structure issized to urge the coaption member along a length of the leaflets of thenative mitral valve; and an anchoring structure coupled to the supportstructure, the anchoring structure comprising a positioning arm andmultiple septum attachment arms, the septum attachment arms disposableon either side of an atrial septum to secure a base of the positioningarm penetrating therethrough, the positioning arm sized to position theelongated profile of the coaptation member between the leaflets of thenative mitral valve with the base thereof secured to the atrial septum.2. The device of claim 1, wherein the coaptation member includes aflexible pocket, the flexible pocket comprised of flexible materialdisposed on the support structure, wherein the support structure issized to urge the flexible material along a length of a commissure ofsaid leaflets.
 3. The device of claim 2, wherein the flexible materialis pericardial tissue.
 4. The device of claim 2, wherein the flexiblepocket has a rounded arch-shape.
 5. The device of claim 1, wherein thelength of cross-sectional profile of the coaptation member issubstantially equal to a length of a commissure of the leaflets.
 6. Thedevice of claim 1, wherein the support structure is nitinol.
 7. Thedevice of claim 1, wherein the support structure comprises a ring. 8.The device of claim 7, wherein the ring is sized to press against wallof a left atrium.
 9. The device of claim 7, wherein the ring is sized toanchor the device within a commissure of the mitral valve.